X-ray imaging apparatus

ABSTRACT

An electronic cassette accommodating a sensor for converting radiation into an electric signal. A cable with a specific length is connected to a side surface of the electronic cassette. A connector that is connectable with a wireless communication unit or an external power source is provided at an end of the cable.

This application is a continuation application of U.S. patentapplication Ser. No. 10/715,723 filed on Nov. 14, 2003, which is hereinincorporated by reference.

BACKGROUND OF THE INVENTION

1. Filed of the Invention

The present invention relates to an X-ray imaging apparatus used formedical diagnosis and particularly relates to a portable imagingapparatus having an area sensor serving as an X-ray receiving medium inwhich multiple photoelectric conversion elements are two-dimensionallyarranged on the same plane.

2. Related Background Art

It is a widely used method, in the field of nondestructive inspectionfor industrial purpose and in the field of medical diagnosis, to obtaina radiation image of an object to be imaged by irradiating the object tobe imaged with radiation and detecting the intensity distribution of theradiation that has been transmitted through the object to be imaged.Specifically, a general method of obtaining a radiation image of anobject includes the steps of preparing a combination of a silver filmand a so-called fluorescent screen (or an intensifying screen) thatemits fluorescent light upon receiving radiation, irradiating an objectto be imaged with X-rays, converting the transmitted radiation intovisible light by means of the fluorescent screen to form an latent imageon the silver film, and then chemically processing the silver film toobtain a visible image. The radiation image obtained by this method isan analogue photograph, which is to be used for diagnosis, inspection orother purposes.

On the other hand, recently there has been developed technology forobtaining a digital image using a two dimensional array sensor as imagereceiving means in which pixels composed of micro photoelectricconversion elements or switching elements are arranged in a lattice-likepattern. Such an imaging apparatus can display obtained image dataimmediately, so that it may be called a direct X-ray digital imagingapparatus. Advantages of the X-ray digital imaging apparatus overconventional analogue photographing technologies are elimination of theneed for films, enlargement of obtained image information realized byimage processing and capability of constructing a database etc.

Digital image data obtained from an X-ray digital imaging apparatus istransferred to a system control unit or a storage server etc. via wiredor wireless data transmission.

X-ray imaging apparatuses for forming still images for medical use arecategorized, based on the scheme of imaging of a patient as an object tobe imaged, into stationary type apparatuses and portable typeapparatuses. An example of the stationary type apparatus is providedwith a table and an imaging portion containing a film or a photoelectricconversion apparatus and it radiates X-rays to a patient from above toobtain an abdominal image of the patient. The portable type apparatususes a lightweight box called a cassette in which a film isaccommodated. The portable type apparatus is used in the case that thecondition of a patient is too bad to be brought from a bed in a ward toa table in an X-ray room in which a stationary type apparatus isinstalled or in the case that a special imaging method that cannot beput into practice by a stationary apparatus is required. In the formercase, an operator brings a cassette and an portable X-ray imagingapparatus to the patient's ward, so that the operator performs imagingin the ward.

In view of portability and operationality, it is desirable that theportable apparatus be made as compact and lightweight as possible.However, in the case that the X-ray digital imaging apparatus is to beconstructed as a portable apparatus (which will be referred to as anelectronic cassette hereinafter), the apparatus includes, in order tooutput an X-ray transmission image of a patient as a digital image data,many components such as a two-dimensional array sensor for receiving anX-ray image, a drive circuit for driving the sensor in accordance with acontrol signal sent from an X-ray generating apparatus, an amplifier forselecting matrices within the sensor by means of the drive circuit toamplify the data of each matrix, an A/D conversion circuit forconverting the output of the amplifier into digital data and a circuitfor serializing the image data that has been sequentially digitized bythe A/D converting circuit and the drive circuit. Therefore, it isdifficult to make the electronic cassette compact and lightweight ascompared to the film cassette. In addition, in the case that wirelessdata transmission is adopted, a memory for temporally storing data and abattery for supplying power to the electronic cassette are furtherrequired. This leads to an additional increase in the size and weight ofthe electronic cassette. In the case that the number of times of imagingwith the electronic cassette is small, the size of the memory and thebattery can be made small, so that an increase in the weight may besmall. However, in order to eliminate the risk of overflow of memoryduring imaging and the risk of running out of battery, and since thetransfer rate of wireless connection is lower than that of wiredconnection, the wired connection should also be taken intoconsideration. On the other hand, in the case that the number of timesof imaging is large, it is desirable that the connection scheme bespecialized to the wired (or cable) connection, the circuitry for wireddata transferring be contained in the electronic cassette, which shouldbe made as compact and lightweight as possible, and a cable for thewired connection be connected to the electronic cassette only at thetime of imaging and data transmission.

FIG. 6 shows an example of a state of use of an electronic cassette thatcan be connected with a cable. The patient P shown in FIG. 6 is apatient lying on a bed 48 in a ward. The condition of the patient P isso bad that he or she cannot be brought to an X-ray room in which astationary X-ray imaging apparatus is installed. Therefore, an operator(not shown) brings an electronic cassette 49 and an portable X-raygenerating apparatus 34 to the patient's ward so as to perform imaging.The electronic cassette 49 can be detachably connected with a cable 5,through which data is transmitted and electric power is supplied, via aconnector 50. The cable 5 is connected to a system control portion 27and a power source portion 28 of the electronic cassette 49. The systemcontrol portion 27 controls the operations of the overall system such ascontrol commands to the electronic cassette 49, receiving of digitalimage data and communication with the portable X-ray generatingapparatus 34 etc. The power source portion 28 transforms an AC voltageof a commercial power source into a predetermined DC voltage for theelectronic cassette 49 to supply it to the electronic cassette 49. Thesystem control portion 27 and the power source portion 28 areaccommodated in the same case having wheels (not shown) with a view toimproving portability. The cable 5 is a composite cable including asignal line between the electronic cassette 49 and the control portion27 and a power supply line between the electronic cassette 49 and thepower source portion 28. Though two wires for a power system and asignal system respectively are included in the same cable, the wires areseparated into a signal line and a power line at the cable end facingthe power source portion 28 and the cable end facing the electroniccassette 49.

In one example of imaging, as a first step of the imaging process, theoperator inserts the electronic cassette 49 that is not connected withthe cable 5 between the patient P and the bed 48 at the position asshown in FIG. 7. The insertion is normally performed from a side of thepatient as shown in FIG. 6. The reason why the electronic cassette 49 isinserted under the unconnected state is to eliminate the troublesomeoperation of determining the position of the electronic cassette whilepaying attention to the cable so that the cable will not fall into theimaging area. The electronic cassette 49 is positioned at the area inwhich an image of the patient to be obtained. After the electroniccassette 49 is positioned, the cable 5 is connected to the connector 50.Then, the operator performs, via an interface 30 of the system controlportion 27 various setting such as setting of imaging conditionsnecessary for imaging (the X-ray tube voltage, the tube current and theX-ray irradiation time etc), imaging timing, image processingconditions, patient's ID, method of processing input images. Theinterface 30 includes a touch panel, a mouse, a keyboard or a footswitch etc. The system control portion 27 drives the portable X-raygenerating apparatus 34 and the electronic cassette 49 based on the setimaging conditions. The portable X-ray generating apparatus 34 includesan X-ray tube 35 and an X-ray stop 37. The X-ray tube 35 is driven by apower source 36 for generating a high voltage controlled by the systemcontrol portion 27 to radiate an X-ray beam. The X-ray stop 37 shapesthe X-ray beam in accordance with a change in the imaging area so thatunnecessary X-ray irradiation is not performed. The X-ray beam isdirected to the patient P lying on the bed 48. The electronic cassette49 is irradiated with the X-ray beam that has been transmitted throughthe patient P. The electronic cassette 49 accommodates a scintillatorfor converting X-rays into visible light and a photo detector array asan X-ray receiving medium in which thin film transistors (TFT) arearranged similar to those disclosed in Japanese Patent ApplicationLaid-Open No. 08-116043. An X-ray image of the patient that has beenirradiated with the X-ray beam is converted into visible light by thescintillator in the interior of the electronic cassette 49 and theresultant visible light is subjected to photoelectric conversion in thephoto detector array. After that, amplification processing and A/Dconversion processing are performed, so that serialized digital imagedata is sent from the electronic cassette to the system control portion27 via the signal line of the cable 5. The system control portion 27performs switching of data to be displayed on a monitor 31, real timecorrection and spatial filtering of the digital image data, toneprocessing, DR compression etc. The processed image is displayed on themonitor 31. The processed digital data is stored in a memory apparatus38 at the same time with the real time image processing. Preferably, thememory apparatus 38 is a data storage apparatus that meets largecapacity, high speed and high reliability requirements. For example,hard disk arrays such as RAID are preferable. After the data is stored,the cable 5 is disconnected from the connector 50 and the electroniccassette 49 is drawn out from between the patient P and the bed 48. Thusthe imaging process is terminated.

The system control portion 27 is provided with a LAN board (not shown),through which the system control portion 27 can be connected to a LAN. Afile server in which image data is to be filed, an image printer foroutputting an image on a film and an image processing terminal forfacilitating complex image processing and diagnosis etc. are connectedto the LAN. The system control portion 27 outputs digital image data inaccordance with a predetermined protocol (for example, DICOM). After theimaging of the patient P is finished, the operator brings the system toa site at which a port for allowing connection to the LAN is availableso as to perform an output operation. The port may be provided in theward in which the patient P stays so that the output operation may beperformed immediately after the completion of imaging.

(Reference: Japanese Patent Application Laid-Open No. 2002-82172)

However, the above-described structure of the electronic cassettesuffers from the following problems.

FIG. 8 shows a case in which a connector provided on an electroniccassette 51 having the structure same as the above-described electroniccassette 49 is present between a patient P and a bed 48. This situationcan occur in the case that the outer size of the electronic cassette 51is smaller relative to the patient P. This is the case for example whenthe width of the body of the patient P is larger than the standard widthor when the outer size of the electronic cassette is equivalent to the12×10 inches size or 10×8 inches size in the case of the film cassette.When the operator places the electronic cassette in position, the cable5 has not been connected yet. Then, it is necessary for the operatoreither to connect the cable while raising up the patient P or to oncedraw out the electronic cassette 51 and move the electronic cassette toa position which allows connection with the cable 5 so as to connect thecable. In any case, it is necessary to change the position relative tothe patient P. In addition, there is a risk that the position of theelectronic cassette can be displaced and the part to be imaged candeviate from the imaging area. In that case, imaging must be performedagain. In addition, since the portable cassette is used not only in theabove-described imaging manner but also in various positions for apatient who cannot move, it is necessary for the operator to performimaging while always paying attention to the position of the connectorof the electronic cassette. This is troublesome for the operator.

SUMMARY OF THE INVENTION

Under the above-described situations, an object of the present inventionis to provide an X-ray imaging apparatus that has an improved cableconnectability.

According to one aspect of the present invention, there is provided anX-ray imaging apparatus comprising:

a sensor for converting radiation into an electric signal;

an electronic cassette for accommodating the sensor;

a first cable connected to a side surface of the electronic cassette;and

a first connector provided at an end of the first cable.

According to another aspect of the present invention, there is providedan X-ray imaging apparatus comprising:

a sensor for converting radiation into an electric signal;

an electronic cassette for accommodating the sensor;

a first cable connected to a side surface of the electronic cassette;and

a first connector provided at an end of the first cable;

a second connector to be connected to the first connector;

a second cable connected to the second connector; and

an external apparatus connected to the second cable fortransmitting/receiving an electric signal to/from the electroniccassette via the first and second cables and/or supplying electric powerto the cassette.

Other features and advantages of the present invention will be apparentfrom the following descriptions taken in conjunction with theaccompanying drawings, throughout which like reference charactersdesignate the same or similar parts.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are incorporated in and constitute apart of the specification, illustrate embodiments of the invention and,together with the description, serve to explain the principle of theinvention.

FIGS. 1A and 1B show the structure of an X-ray imaging apparatus.

FIG. 2 shows the structure of a rectangular electronic cassette and acable

FIG. 3 shows the structure of an electronic cassette and a cable.

FIG. 4 shows a internal structure of an electronic cassette.

FIG. 5 shows connection of an electronic cassette and a wirelesscommunication unit.

FIG. 6 shows the structure of an electronic cassette according to aprior art.

FIG. 7 shows the structure of an electronic cassette according to aprior art.

FIG. 8 shows the structure of an electronic cassette according to aprior art.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

Preferred embodiments of the present invention will be described indetail with reference to the accompanying drawings.

The present invention as defined by the claims will be described basedon embodiments illustrated in the drawings.

FIGS. 1A and 1B are diagrams showing the structure of a firstembodiment. Parts equivalent to those in the previously mentioneddrawings will be designated by the same reference characters.

What is different in this embodiment from the electronic cassette 49shown in FIG. 6 is that a cable 2 is connected to the case of anelectronic cassette 1 and a connector 3 is provided at the end of thecable 2. In FIG. 1B, L1 represents the distance from the side surface ofthe electronic cassette 1 to which the cable 2 is connected to the endof the cable 3, and X1 represents the distance from the center C of theimaging area 4 of the electronic cassette 1 to the aforementioned sidesurface of the electronic cassette 1. The electronic cassette 1 has aconnection port for the cable 2 provided on the aforementioned sidesurface. In FIG. 1A, Wp represents the shoulder width or the maximumbody width defined by Japanese Industrial Standards (JIS) Z8500(directed to measurement of human body), and line O represents thecenter line of the body axis.

In the case shown in FIG. 1A, the center C of the imaging area 4 of theelectronic cassette 1 is positioned on the center line of the body axisO and a cable 5 is connected to the connector 3. In this state, sincethe electronic cassette 1 is placed between the patient P and the bed48, it is difficult for an operator to visually observe the electroniccassette 1. However, in the electronic cassette 1, since the connector 3is spaced apart from the body of the electronic cassette 1 on theconnection side A via the cable 2, the operator can connect it with thecable 5 as long as the connecter 3 projects outside the area of the bodyof the patient P. The cable 5 is used for power supply to the electroniccassette 1 and signal transmission after it is connected, as has beendescribed in connection with FIG. 6.

If the distance L1 is set in the range that satisfies the formula L1Wp/2−X1, the connector 3 will be either at a position in the vicinity ofthe side face of the body of the patient P facing the connection side Aat least or at a position in which the connector 3 projects outside thearea of the body of the patient P, and therefore the operator canconnect the connector 3 and the cable 5 shown in FIG. 1A easily. By wayof example, it is assumed here that the size of the electronic cassetteis JL10×12 size defined by Japanese Industrial Standards (JIS) Z4905 andthe Wp is 45 cm, which is approximately the average shoulder width ofJapanese adult males. The cable connection side is a long side of theelectronic cassette 1. In the case that the aforementioned long side isused as the connection side, X1 is equal to 281.5/2 mm. Therefore, if L1is larger than 84.25 mm, the cable connecting operation will be easilyperformed. If Wp in the above formula is set to the maximum body width,the cable will further projects outside the area of the body. This makesthe connecting operation easier.

Since the distance L1 is a function of X1 mainly, when the size of theelectronic cassette is increased, L1 becomes relatively small. While inthe situation shown in FIG. 1A, the center C of the imaging area 4 islocated on the center line of the body axis O, in the case that theelectronic cassette 1 is to be placed in such a way that the center C ofthe imaging area 4 is at a position above (in the plane of FIG. 1A) thecenter line of the body axis O, the operator can connect the cable in amanner similar to the above by changing, before placing the electroniccassette 1, the orientation of the connection side surface of theelectronic cassette 1 in such a way that the connector 3 projects towardthe connection side B.

FIG. 2 is a diagram showing the structure of a second embodiment of thepresent invention. In FIG. 2, the parts same as those in the previouslymentioned drawings are designated by the same reference characters.

What is different in this embodiment from the electronic cassette 1shown in FIGS. 1A and 1B is that the electronic cassette has asubstantially rectangular shape, the connection port for a cable 7 isprovided on a long side of it, and a connector 8 is provided at the endof the cable 7. The imaging area 9 also has a substantially rectangularshape. In the situation shown in FIG. 2, the electronic cassette 6 isdisposed in such a way that its long side is perpendicular to the centerline of the body axis O of the patient P. Therefore, the connection portfor the cable 7 can hardly be visually observed, since it is beneath thebody of the patient P. However, letting L2 be the distance from the sidesurface of the electronic cassette 6 to which the cable 7 is connectedto the end of the connector 8, and letting X2 be the distance from thecenter C of the imaging area 9 of the electronic cassette 6 to theabove-mentioned side surface of the electronic cassette 6, when thedistance L2 satisfies the formula L2 Wp/2−X2, the connector 8 will beeither at a position in the vicinity of the side face of the body of thepatient P facing the connection side A at least or at a position inwhich the connector 8 projects outside the area of the body of thepatient P, and therefore the operator can connect the connector 8 andthe cable 5 shown in FIG. 1A easily.

As per the above, since L1 and L2 do not represent the cable length butthe distance from the side surface of the electronic cassette to theconnector, they do not depend on the position of the connection port forthe cable.

FIG. 3 is a diagram showing the structure of a third embodiment of thepresent invention. In FIG. 3, the parts same as those in the previouslymentioned drawings are designated by the same reference characters.

What is different in this embodiment from the electronic cassette 49shown in FIG. 6 is that a cable 11 is connected to the case of anelectronic cassette 10 and a connector 12 is provided at the end of thecable 11. In FIG. 3, L3 represents the distance from the side surface ofthe electronic cassette 10 facing the connection side A to the end ofthe cable 12, and X3 represents the distance from the center C of theimaging area 13 of the electronic cassette 10 to the aforementioned sidesurface of the electronic cassette 10. The electronic cassette 10 has aconnection port for the cable 11 provided on the aforementioned sidesurface. In addition, Wt represents the width of the bed 48.Specifically, the width Wt represents the width of the bed 48 in thedirection perpendicular to the body axis of the patient P.

In the case shown in FIG. 3, it is difficult for the operator tovisually observe the electronic cassette 10, since the electroniccassette is placed between the patient P and the bed 48.

If the distance L3 is set in the range that satisfies the formula L3Wt/2−X3, the connector 12 will be either at a position in the vicinityof the side face of the body of the patient P facing the connection sideA at least or at a position in which the connector 12 projects outsidethe area of the body of the patient P even if the center C of theimaging area 13 of the electronic cassette 10 is positioned on thecenter line with respect to the width of the bed 48, in other words ifthe electronic cassette 10 is positioned at the position farthest fromthe both sides of the bed 48. Therefore the operator can connect theconnector 12 and the cable 5 shown in FIG. 1A easily. After connected,the cable 5 is used for power supply to the electronic cassette 10 andsignal transmission, as has been described in connection with FIG. 6. Byway of example, it is assumed here that the size of the electroniccassette is JL10×12 size defined by Japanese Industrial Standards (JIS)Z4905 and Wt is 90 cm. The cable connection side is a long side of theelectronic cassette 1. In the case that the aforementioned long side isused as the connection side, X3 is equal to 281.5/2 mm. Therefore, if L1is larger than 309.25 mm, the cable connecting operation will be easilyperformed.

In the case that the electronic cassette 10 is to be placed at aposition in which the center C is displaced from the center line of thebed 48 toward the connection side B, the operator may change, beforeplacing the electronic cassette 10, the orientation of the connectionside surface of the electronic cassette 10 in such a way that theconnector 12 projects toward the connection side B in a manner similarto the embodiment shown in FIGS. 1A and 1B. While in the presentembodiment the formulation is made with reference to the width of thebed, it may be made with reference to the width of a top plate ofimaging table used in X-ray imaging room directly.

Furthermore, in the arrangement shown in FIG. 3, the connection port forthe cable 11 is provided on the connection side surface of theelectronic cassette 10. However, since L3 does not represent the cablelength but the distance from the side surface of the electronic cassetteto the connector, it does not depend on the position of the connectionport for the cable.

FIG. 4 is a diagram showing the structure of a fourth embodiment, inwhich the interior of an electronic cassette 14 is illustrated. In FIG.4, the parts same as those in the previously mentioned drawings aredesignated by the same reference characters.

The electronic cassette 14 is mainly composed of a scintillator 15, aphoto detector array 16, an X-ray exposure dose monitor 17, an electriccircuit board 18, a connection controller 19, a cable 20, a connector 21and an indicator 22. On the electric circuit board 18, there is mounteda drive circuit 23, an amplifier 24, an A/D conversion circuit 25 and aserializing circuit 26. In addition, cable wiring for signaltransmission and power transmission between those components is alsoprovided. On the other hand, a cable 5 for connecting a system controlportion 27 and a power source portion 28 to the electronic cassette 14is provided with a connector 29 to be connected with the connector 21.

Next, operations of the electronic cassette 14 and the system controlportion under different connection states will be described.

First, under the state in which the connector 21 of the electroniccassette 14 side is not connected with the connector 29 of the systemcontrol portion 27 and the power source portion 28 side, the componentsin the electronic cassette 14 do not operate, since power is notsupplied to the electronic cassette 14. In addition, the indicator 22provided in the connector is not supplied with power, and therefore itdoes not emit light. The system control portion 27 detects that theconnection has not been established, based on absence of communicationwith the connection control portion 19 and sends a command to a monitor31 for displaying input information from interface 30 and image data, tocause the monitor 31 to display a content indicating the disconnectedstate.

When the operator connects the connector 21 on the electronic cassette14 side and the connector 29 on the system control portion 27 and thepower source portion 28 side after placing the electronic cassette 14 inposition, electric power is supplied from the power source portion 28 tothe connection control portion 19 via the cable 20 and the power supplycable 32. Upon receiving power supply, the connection control portion 19recognize the connection. Once the connector 5 and the connector 20 areconnected, power is also supplied to the indicator 22. Then theconnection control portion 19 causes the indicator to emit blue orbluish light to indicate that the electronic cassette 14 is out ofimaging operation and detachment is allowed, until the connectioncontrol portion 19 receives a command signal for imaging from the systemcontrol portion 27. Under this state, the power source portion 28 onlysupply power required for operations of the components of the connectioncontrol portion 19 and the indicator 22. In other words, power has notbeen supplied to each component of the sensor via the power supply cable32 yet. The connection control portion 19 informs the system controlportion 27 of the fact that the connection with the electronic cassette14 has been established via the signal cable 33. Based on thisinformation, the system control portion 27 sends a command to themonitor 31 to cause it to display a content indicating that theelectronic cassette 14 is in a detachable state.

Next, the operator enters through the interface 30 an imaging startcommand for the system control portion 27 in order to perform theimaging operation. Upon receiving the command, the system controlportion 27 transmits a start command to the connection control portion19. In response to the start command, the connection control portion 19transmits a command to the indicator 22 to cause the indicator to emitred or redish light indicating that detachment is not allowed.

At the same time, the system control portion 27 sends a command to themonitor 31 to cause it to display a content indicating that detachmentis not allowed.

After the above-described operations are completed, the system controlportion 27 commands the power source portion 28 so that electric powerrequired for driving of the components of the sensor is supplied fromthe power source portion 28 via the power supply cable 32. At the sametime, the system control portion 27 transmits an imaging command signalto the electric circuit board 18 via the signal cable 33. In addition,the system control portion 27 drives the X-ray tube 35 of a portableX-ray generating apparatus 34 by means of a high voltage generatingpower source 36, drives an X-ray stop 37 to set an irradiation field,and causes an X-ray beam to be radiated. The drive circuit 23 on theelectric circuit board 18 detects an X-ray exposure termination signalfrom the X-ray exposure dose monitor 17, high voltage power applicationfrom the high voltage generating power source 36 or an X-ray tubecurrent signal to drive the TFT switches so as to read out electriccharges. In the scintillator 15, the base material of the phosphor isexited by high energy X-rays and fluorescence within the visible lightrange is generated by recombination energy released upon recombination.The fluorescence is either based on the base material itself such asCaWO4 or CdWO4 or a luminescence center material such as CSI:Ti orZnS:Ag activated in the base material.

The photo detector array 16 is provided in close contact with thescintillator 15. The photo detector array 16 converts light generated inthe scintillator 15 into an electric signal. The X-ray exposure dosemonitor 17 is provided for monitoring the X-ray exposure dose. The X-rayexposure dose monitor 17 directly detect X-rays using a light receivingelement made of crystal silicon. Visible light transmitted through thephoto detector array 16 is detected by an amorphous silicon lightreceiving element laminated on the backside of the substrate of thephoto detector array 16. The detected information is transmitted to thesystem control portion 27, so that the system control portion 27 drivesthe high voltage generating power source 36 to stop or adjust the X-raysbased on that information. The drive circuit 23 drives the photodetector array 16 under a control of the system control portion 27 toread out a signal from each pixel. Matrices in the sensor are subjectedto selection by the drive circuit 23 and digital image data is obtainedby processing data of each matrix by the amplifier 24 for amplifying thedata, the A/D conversion circuit 25 for converting the output of theamplifier into digital data and the serializing circuit 26 forserializing the image data that has been sequentially digitized by theA/D conversion circuit 25 and the drive circuit 23. The obtained digitalimage data is transmitted to the system control circuit 27 and stored ina recording apparatus 38.

After the transmission of the digital image data to the system controlportion 27, the power source portion 28 stops power supply to thecomponents of the sensor based on a command by the system controlportion 27.

After the digital image data has been stored in the recording apparatus38 and the system control portion has sent the stop command to the powersource portion 28, the system control portion 27 transmits an imagingtermination command to the connection control portion 19 via the signalcable 33. Upon receiving the command, the connection control portion 19transmits a command to the indicator 22 to cause it to emit bluish lightso as to indicate that detachment of the electronic cassette 14 isallowed. Under this state, the operator may disconnect the connector 21and the connector 29. The system control portion 27 sends a command tothe monitor 31 to cause it to display a content indicating thatdetachment of the electronic cassette 14 is allowed.

After checking the indicator or the display on the monitor 31, theoperator disconnects the connector 21 and the connector 29 to detach theelectronic cassette 14. Thus, the imaging operation on the patient P isfinished. The filing of the stored digital image data is performed inthe manner same as that described in connection with the prior art.

As per the above, with the provision of the indicator, the operator canrecognize the operation state of the electronic cassette. Consequently,it is possible to avoid damage on the sensor circuit that can be causedby instantaneous power shutdown due to abrupt disconnection of theconnectors while the power is supplied to the sensor. In addition, sincethe indicator is provided on the connector to be connected, the operatorcan easily check the indicator as described in the previous embodiment.

FIG. 5 is a diagram showing the structure of a fifth embodiment, inwhich the interior of an electronic cassette 39 is illustrated. In FIG.5, the parts same as those in the previously mentioned drawings aredesignated by the same reference characters.

In this embodiment, an image memory 40 and a battery 41 are additionallyprovided in the interior of the electronic cassette 39 as componentsdifferent from those in the electronic cassette 14 show in FIG. 4. Inaddition, a wireless communication module 42, a connector 43 that can beconnected with a connector 29 and a control portion 44 for controllingthe communication scheme and operations of the electronic cassette 39are provided. The system control portion 27 is additionally providedwith a wireless communication terminal 45 for communicating with thewireless communication module 42. With the provision of the image memory40, the battery 41 and the wireless communication module 42, theoperator can use the electronic cassette 39 on the cableless basis (i.e.without a cable). In the following, the operations of the componentswill be described.

In the state shown in FIG. 5, nothing is connected to the connector 43of the electronic cassette 39. Under this state, the control portion 44suspends power supply to each component of the sensor from the battery41 in accordance with the unconnected state of the connector 43. Thesystem control portion 27 detects that the connection has not beenestablished based on absence of communication with the control portion44 of the electronic cassette 39 and sends a command to a monitor 31 fordisplaying input information from interface 30 and image data, to causethe monitor 31 to display a content indicating the disconnected state.

In the case that the electronic cassette 39 is to be used without thecable, the operator connects the wireless communication module 42 withthe connector 43. Then, in response to the connection of the wirelesscommunication module 42, the control portion 44 sends a command to causethe battery 41 to supply power to the wireless communication module 42.Thus, the wireless communication module 42 is supplied with power fromthe electric energy stored in the battery 41 in advance so as to be inan operable state. At that time, the battery 41 supplies only the powerrequired for the operations of the components of wireless communicationmodule 42. In other words, power has not been supplied to eachcomponents of the sensor via a power supply cable 46 yet. The controlportion 44 informs the wireless communication terminal 45 of the factthat wireless communication module 42 has been connected with theelectronic cassette 39, through the wireless communication module 42.Based on that information from the wireless communication terminal 45,the system control portion 27 sends a command to the monitor 31 to causeit to display a content indicating that the electronic cassette 14 is inan operable state on the cableless basis.

Next, the operator enters through the interface 30 an imaging startcommand for the system control portion 27 in order to perform theimaging operation. Upon receiving the command, the system controlportion 27 transmits a start command to the control portion 44 via thewireless communication terminal 45 and the wireless communication module42. Upon receiving the command, the control portion 44 commands thebattery 41 so that power required for driving of the components of thesensor is supplied from the battery 41 via the power supply cable 46. Atthe same time, the control portion 44 transmits an imaging commandsignal to the electric circuit board 18 via a signal cable 47. Inaddition, the system control portion 27 drives the X-ray tube 35 of theportable X-ray generating apparatus 34 by means of the high voltagegenerating power source 36, drives an X-ray stop 37 to set anirradiation field, and causes an X-ray beam to be radiated. The drivecircuit 23 on the electric circuit board 18 detects an X-ray exposuretermination signal from an X-ray exposure dose monitor 17, high voltagepower application from the high voltage generating power source 36 or anX-ray tube current signal to drive TFT switches so as to read outelectric charges in the manner same as the embodiment shown in FIG. 4.In the scintillator 15, the base material of the phosphor is exited byhigh energy X-rays and fluorescence within the visible light range isgenerated by recombination energy released upon recombination. The photodetector array 16 converts light generated in the scintillator 15 intoan electric signal.

The X-ray exposure dose monitor 17 detects the radiated X-rays totransmit information obtained by the detection to the control portion44. The control portion 44 further transmits the information to thesystem control portion 27 via the wireless communication module 42 andthe wireless communication terminal 45. The system control portion 27drives the high voltage generating power source 36 to stop or adjust theX-rays based on that information. The drive circuit 23 drives the photodetector array 16 under a control of the control portion 44 to read outa signal from each pixel. Matrices in the sensor are subjected toselection by the drive circuit 23 and digital image data obtainedthrough the amplifier 24, the A/D conversion circuit 25 and theserializing circuit 26 is stored in the image memory 40. In addition,the control portion 44 transmits the obtained digital image data to thesystem control portion 27 via the wireless communication module 42 andthe wireless communication terminal 45, so that the digital image datais stored in the recording apparatus 38. Since the data amount of theimage data is large, it is desirable that the frequency of thecommunication wave be in a band of several gigahertz in order to realizecommunication within a short time. The image data stored in the imagememory 40 is temporally data until the image data is stored in therecording apparatus 38, and therefore the control portion 44 controls todelete the image data stored in the image memory 40 when informed by thesystem control portion 27 of completion of the storing of the data inthe recording apparatus 38. At the same time, the control portion 44commands the battery 41 to stop the power supply to the components ofthe sensor. The filing of the digital image data stored in the recordingapparatus 38 is performed in the manner same as that described inconnection with the prior art.

While in this embodiment the wireless communication uses a frequencyband of several gigahertz, the wireless communication module may bereplaced with an optical communication module such as an infraredcommunication module.

As per the above, in the case that the electronic cassette is usedwithout a cable, troublesome handling of the cable can be eliminated,since the operation of connecting a cable is not necessary. However,since power consumption required for the imaging operation with theelectronic cassette is large, it is necessary to increase the capacityof the battery when successive imaging operations are to be enabled. Anincrease in the capacity leads to an increase in the volume and theweight of the battery such as a lithium ion battery. This maydeteriorate operationality of the electronic cassette, which is requiredto be portable and lightweight.

In view of the above situation, in the embodiment shown in FIG. 5, theconnector 43 of the electronic cassette 39 side is adapted to beconnectable with the connector 29 of the system control portion 27 side.When the connector 29 and the connector 43 are connected, the systemcontrol portion 27 and the control portion 44 perform communication andpower supply related to the above-described operations of the electroniccassette 39 through the cables 5 and 20 and the connectors 29 and 43. Inresponse to the connection of the connectors 29 and 43, the controlportion 44 switches the communication path and the power supply path tothe cable basis. At that time, power is not supplied from the powersource portion 28 to the sensor side, but charging of the battery may beperformed if the battery has not been charged up to its full capacity.The control portion 44 informs the system control portion 27 of the factthat electronic cassette 39 is connected with the cable. Upon receivingthat information, the system control portion 27 sends a command to themonitor 31 to cause the monitor to display a content indicating that theelectronic cassette is in an operable state on the cable basis. Next,the operator enters through the interface 30 an imaging start commandfor the system control portion 27 in order to perform the imagingoperation. Upon receiving the command, the system control portion 27transmits a start command to the control portion 44. At the same time,the system control portion 27 causes the power source portion 28 tosupply power required for driving the components of the sensor of theelectronic cassette 39. On the other hand, the control portion 44transmits an imaging command signal to the electric circuit board 18 viathe signal cable 47. The system control portion 27 sends the commandsame as that described before to the portable X-ray generating apparatus34 so as to cause an X-ray beam to be radiated. In addition, the systemcontrol portion 27 and the control portion 44 perform the series ofcommunications same as those described before on the cable basis, sothat the obtained image data is stored in the recording apparatus 38.Then, the system control portion 27 commands the power source portion 28to stop the power supply to the components of the sensor.

As per the above, imaging may be performed with a cable in the case thatmany imaging operations are to be performed successively, and thereforeimaging can be performed without deteriorating portability of theelectronic cassette. While in this embodiment the wireless communicationmodule is constructed as a detachable module, the wireless module may beaccommodated in the electronic cassette in the case the cassette is usedin most cases for a small number of times of imaging on the cablelessbasis.

As has been described in the foregoing, the X-ray imaging apparatusaccording to the present invention has a connecting portion forconnection with an external apparatus provided at a position within aprescribed distance range from the body of the electronic cassette. Withthis feature, it can be connected with the external apparatus easilyirrespective of the size of the electronic cassette or the body type ofthe patient. In addition, with the provision of indication of theconnection state at the connecting portion, whetherattachment/detachment is allowed or not can be easily recognized.Furthermore, with the provision of the wireless communication module atthe connecting portion, communication means can be selected inaccordance with the state of use of the electronic cassette.

OTHER EMBODIMENT

Note that the present invention may be applied to either a systemconstituted by a plurality of apparatuses (e.g. an image processingapparatuses, interfaces, radiographic apparatuses, X-ray generationapparatuses, and the like) or an arrangement that integrates an imageprocessing apparatus and a radiographic apparatus, or the like.

The present invention is not limited to the above embodiments andcarious changes and modifications can be made within the sprit and scopeof the present invention. Therefore to apprise the public of the scopeof the present invention, the following claims are made.

1. An X-ray imaging apparatus comprising: a sensor for convertingradiation into an electric signal; an electronic cassette foraccommodating the sensor; a connector for connecting the electric signaland a cable; and a control unit for controlling the connector to eithera condition where the cable can be disconnected from the connector or acondition where the cable cannot be disconnected from the connector onthe basis of photographing driving of the electronic cassette.
 2. AnX-ray imaging apparatus according to claim 1, further comprising: asystem control unit for controlling the photographing driving of saidelectronic cassette, which is connected to said cable, wherein saidcontrol unit controls said connector in accordance with a signal fromthe system control unit.
 3. An x-ray imaging apparatus according toclaim 1, wherein said electronic cassette is provided with an indicator,the indicator emitting light of a specific color in accordance with acondition whether said cable can be disconnected from said connector ornot.
 4. An X-ray imaging apparatus according to claim 1, wherein saidelectronic cassette is provided with a wireless communication unitcapable of communicating with an external apparatus, the wirelesscommunication unit being connectable to said connector.
 5. An X-rayimaging apparatus according to claim 4, wherein said electronic cassetteis provided with a battery for supplying electric power and said controlunit is controlled so as electric power to be supplied to said wirelesscommunication unit from the battery when the wireless communication unitis connected to said connector.
 6. An X-ray imaging apparatus accordingto claim 1, wherein said electronic cassette is provided with a batteryfor supplying electric power and said control unit controls so aselectric power to be supplied to said sensor from the battery when saidcable is disconnected from said connector.
 7. An X-ray imaging apparatuscomprising: a sensor for converting radiation into an electric signal;an electronic cassette for accommodating the sensor; a first cableconnected to a side surface of the electronic cassette; a connectorprovided at an end of the first cable; a second cable to be connected tothe first connector; and an external apparatus connected to the secondcable for transmitting/receiving an electric signal to/from theelectronic cassette via the first and second cables, wherein a length Lof the first cable is determined based on the distance formulated by LWp/2 or L Wp/2−X, where X represents a distance from a center of thesensor to the side surface of said electronic cassette and Wp representsa shoulder width or a maximum body width of a human body defined byJapanese Industrial Standards Z8500.
 8. An X-ray imaging apparatusaccording to claim 7, wherein said electronic cassette comprises acontrol unit for controlling said second cable to either a conditionwhere said second cable can be disconnected from said connector or acondition where the second cable cannot be disconnected from theconnector, and the control unit controls the connector in accordancewith a signal from said outer apparatus.
 9. An x-ray imaging apparatusaccording to claim 8, wherein said electronic cassette is provided withan indicator, the indicator emitting light of a specific color inaccordance with a condition whether said cable can be disconnected fromsaid connector or not.
 10. An X-ray imaging apparatus according to claim9, wherein said electronic cassette is provided with a wirelesscommunication unit capable of communicating with an external apparatus,the wireless communication unit being connectable to said connector. 11.An X-ray imaging apparatus according to claim 10, wherein saidelectronic cassette is provided with a battery for supplying electricpower and said control unit is controlled so as electric power to besupplied to said wireless communication unit from the battery when thewireless communication unit is connected to said connector.
 12. An X-rayimaging apparatus according to claim 11, wherein said electroniccassette is provided with a battery for supplying electric power andsaid control unit controls so as electric power to be supplied to saidsensor from the battery when said cable is disconnected from saidconnector.
 13. An X-ray imaging apparatus comprising: a sensor forconverting radiation into an electric signal; a battery for supplyingelectric power to the sensor; an electronic cassette for accommodatingthe sensor; a first cable connected to a side surface of the electroniccassette; a connector provided at an end of the first cable; a secondcable to be connected to the first connector; and an external apparatusconnected to the second cable for transmitting/receiving an electricsignal to/from the electronic cassette via the first and second cables,wherein electric power is supplied to the sensor from the battery if theconnector and the second cable are not connected each other, electricpower is supplied to the sensor from the external apparatus if theconnector and the second cable are connected each other.
 14. An X-rayimaging apparatus according to claim 13, wherein said electroniccassette includes an analog-digital converter foranalog-digital-converting said electric signal and said wirelesscommunication unit capable of communicating with said outer apparatus,the electronic cassette sends a digital data obtained by theanalog-digital conversion from the wireless communication unit if saidconnector and said second cable are not connected each other.
 15. AnX-ray imaging apparatus according to claim 12, wherein said electroniccassette comprises a control unit for controlling under either acondition where said second cable can be disconnected from saidconnector or a condition where the second cable cannot be disconnectedfrom the connector, and the control unit controls the connector inaccordance with a signal from said outer apparatus.